WO2013115018A1

WO2013115018A1 - Optical coherence tomography device and optical coherence tomography method

Info

Publication number: WO2013115018A1
Application number: PCT/JP2013/051248
Authority: WO
Inventors: 山田　朋宏
Original assignee: キヤノン株式会社
Priority date: 2012-01-31
Filing date: 2013-01-23
Publication date: 2013-08-08
Also published as: US9551564B2; JP2013178235A; WO2013115018A9; JP5984693B2; US20130278935A1

Abstract

With a conventional OCT device, a k-trigger emission unit and a measurement assembly for obtaining a coherence light beam having information of an object are separate, requiring sending a trigger signal for sampling from the k-trigger emission unit to the measurement assembly, thus making it easier for timing errors from a plurality of electrical devices to accumulate, and complicating high-precision synchronization. Provided is an OCT device, comprising: a light source unit which changes a wavelength of light; a coherent optical assembly which splits a light beam from the light source unit into an illumination light beam which illuminates an object and a reference light beam, and causes a coherent light from reflected light of the light beam with which the object is illuminated and the reference light beam; an optical detection unit which receives the coherent light beam; and an information acquisition unit which acquires information of the object on the basis of a time waveform of the intensity of the coherent light beam. The OCT device further comprises a wavelength selection apparatus which is disposed upon a light beam path between the light source unit and the optical detection unit and which has an equal frequency gap wavelength selection feature. The information acquisition unit acquires a peak value of the time waveform of the intensity of the coherent light beam and acquires information of the object on the basis of the acquired peak value.

Description

Optical coherence tomography apparatus and optical coherence tomography method

The present invention relates to an optical coherence tomography apparatus and an optical coherence tomography method.

In a conventional optical coherence tomography (OCT) apparatus (hereinafter abbreviated as an OCT apparatus) using a wavelength tunable light source, an object is irradiated with light, the wavelength of the irradiated light is continuously changed, and the reference light And the reflected light returning from different depths of the object. Then, a tomographic image of the object is obtained by analyzing the frequency component included in the time waveform of the intensity of the interference light (hereinafter abbreviated as interference spectrum). The analysis of the frequency component is performed by Fourier transforming the interference spectrum. However, in order to obtain a tomographic image with less distortion and noise, it is necessary to sample the interference spectrum at equal wave intervals and perform the Fourier transform.

Conventionally, in order to sample at an equal wave number interval from the interference spectrum, a part of the irradiation light is branched and monitored by a detector through an interferometer such as an etalon, thereby determining the wave number selection timing. In this way, there are a system (k trigger generation unit) that determines the timing of wave number selection and a system (measurement system) that detects the intensity of interference light, and sampling is performed by synchronizing them. Specifically, the k trigger generation unit samples an interference spectrum at equal wave number intervals by inputting a k trigger (sampling trigger) signal to the measurement system at equal wave number intervals (see Patent Document 1).

JP 2007-24677 A

However, in the conventional OCT apparatus as described above, since the k trigger generation unit and the measurement system are separate, it is necessary for the k trigger generation unit to input a trigger signal for sampling to the measurement system. Errors are easy to accumulate, making high-precision synchronization difficult.

An optical coherence tomographic imaging apparatus (OCT apparatus) according to the present invention divides into a light source unit that changes the wavelength of light, irradiation light that irradiates the object with light from the light source unit, and reference light, and irradiates the object Information of the object is obtained based on an interference optical system that generates interference light by reflected light of the reflected light and the reference light, a light detection unit that receives the interference light, and a time waveform of the intensity of the interference light An optical coherence tomography apparatus having an information acquisition unit that further includes a wavelength selector provided on an optical path between the light source unit and the light detection unit and having wavelength selection characteristics at equal frequency intervals. The information acquisition unit acquires a peak value of a time waveform of the intensity of the interference light, and acquires information on the object based on the acquired peak value.

According to the OCT apparatus according to the present invention, the light from the light source is detected by the light detection unit through the wavelength selector having the wavelength selection characteristics at equal wave number intervals. As a result, data on the intensity of the interference light at regular wave intervals is obtained. Therefore, since it is not necessary to provide the k trigger generation unit and the measurement system as separate optical systems, timing errors are suppressed and high-precision synchronization can be achieved.

It is the figure which showed the structure of the OCT apparatus which concerns on Embodiment 1 of this invention. It is a figure for demonstrating the method to acquire the peak value of the intensity | strength of interference light (light reception voltage) using the OCT apparatus which concerns on Embodiment 1 of this invention. It is a figure for demonstrating an example of a structure of the Fabry-Perot etalon in Embodiment 1 of this invention. It is the figure which showed the structure of the information acquisition part in Embodiment 1 of this invention. It is the figure which showed the flow of the process performed in an information acquisition part before obtaining the tomogram of an object in Embodiment 1 of this invention. It is a figure which shows an example of the graph after the data of the intensity | strength of the received light voltage in Embodiment 1 of this invention before entering into an A / D converter. It is a figure which shows an example of the data of the received light voltage stored in the memory in Embodiment 1 of this invention. It is a figure for demonstrating an example of the method of producing the sampling data in Embodiment 1 of this invention. It is the figure which showed the structure of the OCT apparatus which concerns on Embodiment 2 of this invention. It is a figure for demonstrating the relationship between the received light voltage and frequency which are detected with the photodetector in the Example of this invention. It is a figure which shows the time waveform of the received light voltage obtained by the information acquisition part in the Example of this invention.

Although an optical coherence tomographic imaging apparatus (hereinafter abbreviated as an OCT apparatus) according to an embodiment of the present invention will be described below, the present invention is not limited thereto.

(Embodiment 1)
(OCT equipment)
The OCT apparatus according to the first embodiment will be described with reference to FIGS. In addition, the arrow in a figure has shown the direction where light travels.

The OCT apparatus according to the first embodiment is configured to include at least a light source unit 101, an interference optical system 102, a light detection unit 103, an information acquisition unit 104, and a wavelength selector 105 having wavelength selection characteristics at equal wave number intervals. Although not shown, the information acquisition unit 104 acquires information on the measurement target object. In addition, the information acquisition unit 104 preferably includes a Fourier transformer. Here, if the information acquisition unit 104 has a Fourier transformer, the form is not particularly limited as long as the information acquisition unit 104 has a function of performing Fourier transform on the input data. An example is a case where the information acquisition unit 104 has a calculation unit, and the calculation unit has a function of performing Fourier transform. Specifically, this is a case where the arithmetic unit is a computer having a CPU, and this computer incorporates an application having a Fourier transform function. Another example is a case where the information acquisition unit 104 includes a Fourier transform circuit having a Fourier transform function. The light emitted from the light source unit 101 passes through the interference optical system 102 and is output as interference light having information on the object 113 to be measured. The interference light passes through a wavelength selector (hereinafter simply referred to as a wavelength selector) 105 having wavelength selection characteristics with equal wave number intervals, and is received by the light detection unit 103 at equal wave number intervals. The light detection unit 103 may be a differential detection type or a simple intensity monitor type. Information on the time waveform of the intensity of the interference light received at equal wave intervals is sent from the light detection unit 103 to the information acquisition unit 104. The information acquisition unit 104 acquires the peak value of the time waveform of the intensity of the interference light received at equal wave intervals and performs Fourier transform to acquire information on the object 113 (for example, information on a tomographic image). As described above, since the object information can be obtained without using the k-trigger generator, high-precision synchronization can be achieved. Note that components other than the light source unit 101, the interference optical system 102, the light detection unit 103, the information acquisition unit 104, and the wavelength selector 105 can be arbitrarily provided as long as the object of the present invention is achieved.

In addition, when the information acquisition unit 104 does not have a Fourier transformer, information on an object may be acquired using the maximum entropy method (MEM).

Hereinafter, a detailed description will be given of the process from the generation of light by the light source unit 101 to the acquisition of tomographic image information of the object to be measured.

The light emitted from the light source unit 101 that changes the wavelength of the light passes through the fiber 106 and enters the coupler 107 to be irradiated light passing through the irradiation light fiber 108 and reference light passing through the reference light fiber 109. Branch off. Irradiation light passes through the collimator 110 to become parallel light and is reflected by the mirror 111. The light reflected by the mirror 111 is irradiated to the object 113 through the lens 112 and is reflected from each layer in the depth direction of the object 113. On the other hand, the reference light is reflected by the mirror 115 through the collimator 114. In the coupler 107, the reflected light from the object 113 interferes with the reflected light from the mirror 115. The interfered light passes through the fiber 116, passes through the collimator 117, becomes parallel light, and enters the wavelength selector 105.

On the spectrum of the interference light that has passed through the wavelength selector 105, peaks at equal wave intervals are superimposed. For example, it is assumed that the time waveform of the intensity of the interference light (L1 in FIG. 1) before entering the wavelength selector 105 is represented in FIG. When the wave number of the light emitted from the light source unit 101 and the time are in a linear relationship, sampling is performed by sampling the time waveform of the intensity of the interference light represented in FIG. 2A at equal intervals with respect to the time axis. The obtained data has an equal wave number interval. However, when the wave number of light emitted from the light source unit 101 and the time are not in a linear relationship, the sampled data does not have an equal wave number interval.

Therefore, the wavelength selector 105 having the characteristic that the transmittance becomes a maximum value at equal wave number intervals is used. As the wavelength selector 105, for example, as shown in FIG. 2B, a wavelength selector 105 having a property of having a maximum value 1 of transmittance at equal wave number intervals can be used. In the interference light (L2 in FIG. 1) that has passed through the wavelength selector 105 having such characteristics, peaks at equal wave intervals are superimposed (FIG. 2 (c)). The peak values in the graph of FIG. 2C are at equal wavenumber intervals.

The interference light on which peaks at equal wave intervals are superimposed is collected through the collimator 118 and received by the light detection unit 103. Information on the intensity of the interference light received by the light detection unit 103 is converted into electrical information such as a voltage and sent to the information acquisition unit 104. The information acquisition unit 104 reads the peak value of the time waveform of the intensity of the interference light. Actually, since the time waveform of the intensity of the interference light is converted into the time waveform of the light reception voltage by the light detection unit 103, the peak value of the time waveform of the light reception voltage is read out. For example, when the information acquisition unit 104 acquires information on the received light voltage having the time waveform shown in FIG. 2D, the peak value indicated by the white circle in FIG. Information on a tomographic image of the object 113 is obtained by subjecting the read peak value to Fourier transform using a Fourier transformer. A value obtained by Fourier transforming the peak value corresponds to a frequency component included in the interference light. The frequency component is reflected from the coupler 107 on the object surface and reaches the coupler 107, and from the coupler 107 to the mirror 115. It is proportional to the difference between the length of the optical path reflected by and reaching the coupler 107. Therefore, as information on the tomographic image of the object 113, for example, information on the relationship between the length in the depth direction from the object surface and the intensity of reflected light from each layer of the object 113 can be obtained (FIG. 2 (e)). .

The information of the tomographic image may be sent from the information acquisition unit 104 to the image display unit 119 and displayed as an image. A three-dimensional tomographic image of the object 113 to be measured can be obtained by scanning the mirror 112 in a plane perpendicular to the direction in which the irradiation light is incident. The information acquisition unit 104 may control the light source unit 101 via the electric circuit 120. Although not shown, the intensity of light emitted from the light source unit 101 may be monitored sequentially, and the data may be used for amplitude correction of the signal of the intensity of interference light.

As described above, in the OCT apparatus according to the present embodiment, since the interference light passes through the wavelength selector 105 having the wavelength selection characteristics with equal wave number intervals, the time waveform data of the intensity of the interference light acquired by the light detection unit 103 is obtained. Is an equal wave number interval. That is, the intensity data of the interference light acquired by the light detection unit 103 is data of equiwavenumber intervals, the peak value (white circle in FIG. 2 (d)) is sampled, and Fourier transform is performed to obtain object information. can get. Therefore, the k-trigger generation unit which has been conventionally required is unnecessary, the timing error is suppressed, and high-precision synchronization can be performed.

The wavelength selector 105 only needs to be provided on the optical path between the light source unit 101 and the light detection unit 103. For example, it may be provided on the optical path between the light source unit 101 and the coupler 107, may be provided on the optical path between the coupler 107 and the mirror 115, and is provided between the coupler 107 and the object 113. It may be done. Preferably, the wavelength selector 105 is provided on the optical path between the optical interference system 102 and the light detection unit 103 as shown in FIG. This is because when the wavelength selector 105 is provided between the light source unit 101 and the coupler 107, the amount of light incident on the interference optical system 102 from the light source unit 101 may be reduced, resulting in the coupler 107. This is because the intensity of the interference light may be reduced. Alternatively, when the prescribed amount of light is applied to the object 113 or the like, the amount of emitted light required for the light source unit 101 increases. When the object 113 is a living body such as an eyeball, the intensity of reflected light from the object 113 is weak. Therefore, if the wavelength selector 105 is provided between the coupler 107 and the object 113, the intensity of the reflected light will be further reduced. When the wavelength selector 105 is provided between the coupler 107 and the mirror 115, or when the wavelength selector 105 is between the coupler 107 and the object 113, the wavelength selector 105 is provided only on one arm of the interference optical system. It will be inserted. In this case, noise generated due to the vibration of the wavelength selector 105 becomes noise that cannot be removed even if a differential detection system is used.

(Peak value)
In the present embodiment, the peak value is a maximum value of the intensity of the interference light (light reception voltage). However, if each peak value is an equal wave number interval, a peak value near a maximum value slightly deviated from the maximum value may be used as the peak value. Good.

Here, when the wavelength selector 105 has a characteristic in which the transmittance has a value of 1 at equal wave number intervals and a value of 0 at other wave numbers, the white circle in FIG. Only the peak value of the intensity of the interference light (light reception voltage) shown is received (detected) by the light detection unit 103 and becomes 0 between the peaks. However, as shown in FIG. 2B, the actual wavelength selector 105 has a transmittance value between 0 and 1 at the wave number between them even if the transmittance is 1 at regular wave number intervals. Therefore, as shown in FIG. 2C, interference light other than the peak value is also received. Therefore, it is necessary to read out the maximum value (white circle in FIG. 2D) of each peak as the peak value. In addition, the actual maximum transmittance of the wavelength selector is slightly lower than 1 due to absorption of the medium, but this is not a problem in the present invention.

In addition, the peak value of the time waveform of the intensity of the interference light acquired by the information acquisition unit 104 is the data of the time waveform of the intensity of the interference light received by the light detection unit 103 from the one having the greater intensity of the interference light. It is preferable that the number is as many as the maximum value of the transmittance of the wavelength selector 105.

(Wavelength selector with wavelength selection characteristics at equal frequency intervals)
The wavelength selector in the present embodiment is not particularly limited as long as it is an optical element or optical system having wavelength selection characteristics with equal wave number intervals. For example, as shown in FIG. 2B, a wavelength selector having a maximum value of transmittance at equal wave number intervals can be used. The light that has passed through such a wavelength selector becomes light having peaks at equal frequency intervals on the spectrum. Further, since the intensity value of the interference light (light reception voltage) is sampled at the maximum value of the transmittance, it is preferable that the line width of the peak of the maximum value of the transmittance is narrow. That is, when the wavelength selector is a Fabry-Perot filter, it is preferable that the filter has a narrow band. This is because as the line width of the peak of the maximum value of the transmittance is narrower, it is easier to sample the intensity value of the interference light at equal frequency intervals. For example, when the frequency interval of the sampling light is 18.7 GHz, the line width of the peak of the maximum value of the transmittance of the Fabry-Perot filter is preferably 1/10 or less, and preferably 1/100 or less. Further preferred. This is realized by setting the reflectance of the reflecting mirrors at both ends constituting the Fabry-Perot filter to 75% or more and 97% or more, respectively. The wave number intervals are preferably equal to each other, but may be different from each other to the extent that the effects of the present invention are achieved.

It is also preferable that the line width of the peak of the transmittance maximum value of the filter is narrower than the line width of the light source.

The line width is described by the wavelength width Δλ and the frequency width Δν, and indicates the full width at half maximum or 1 / e ^ 2 full width of the emission spectrum of the light source and the transmittance spectrum of the filter. In the following, the line width will be described as the full width at half maximum of the peak of the wavelength spectrum.

The line width Δλ of the light source is obtained by using an OCT image of a bright object such as a mirror, for example, and changing the optical path length difference between the mirror and the reference mirror of the OCT interferometer so that the brightness of the OCT image becomes 1/2. The coherence length Δz is defined, and can be obtained from the following equation (1) from Δz.

(1)

By passing the interference signal through a filter having a peak width narrower than the line width of the light source, light having a line width narrower than that of the light source can be extracted from the light included in the interference signal. It is. In this case, the obtained interference signal is also an interference signal between lights having a line width narrower than the line width of the light source.

The fact that interference signals between light with narrow line widths can be obtained means that even with respect to the distance at which an OCT image can be acquired, an object is irradiated with light with a narrow band width and the reflected light is acquired to obtain the interference spectrum. It has an effect similar to that obtained.

In other words, when the line width of the filter is narrower than the line width of the original light source, the distance in the depth direction where the OCT image can be obtained can be increased by cutting out the interference light into a narrow band with the filter before light reception.

For example, assuming that the shape of the spectrum cut out by the filter is approximately Gaussian, the imageable depth range Δz in the depth direction when the emission wavelength is λ0 with respect to the full width at half maximum Δλ of the peak wavelength of the filter is This is the value represented by (2).

(2)

As can be seen from the equation, the narrow line width of the peak of the filter corresponds to the small Δλ in the above equation, and as a result, the value of the OCT image obtainable range Δz becomes large.

In general, it is difficult to realize a narrow line width light source capable of sweeping a wide wavelength range at a high speed. Therefore, development of such a high-performance light source itself may be a big problem.

Therefore, according to the present invention, among the above-mentioned performances required for the light source, it is preferable that the requirements regarding the emission line width can be relaxed from the viewpoint of easy development of the light source.

The type of the wavelength selector is not particularly limited, and an optical element such as a Fabry-Perot filter, an optical system such as a Mach-Zehnder interferometer, and a Michelson interferometer can be used. Alternatively, a half mirror facing through an air gap may be used, or a multiple reflection film mirror (Distributed Bragg Reflector, hereinafter abbreviated as DBR) facing each other in an optical fiber may be produced. Among the wavelength selectors according to the present embodiment, a Fabry-Perot filter that easily increases finesse is preferable. An example of the Fabry-Perot filter is a Fabry-Perot etalon.

(Fabry Perot Etalon)
The Fabry-Perot etalon will be described with reference to FIG.
An example of a Fabry-Perot etalon has a configuration in which DBRs 302 are provided on both surfaces of a glass substrate 301. The DBR is composed of a plurality of dielectric films, and the reflectance of the Fabry-Perot etalon can be changed by changing the number of dielectric films and the refractive index of each dielectric film. Increasing the reflectivity increases finesse and increases the wavelength selectivity at equal wave intervals. The glass substrate 301 is not particularly limited, and BK7 or the like can be used.

(Light detector)
The light detection unit in this embodiment will be described. In the light detection part in this embodiment, if the intensity | strength of interference light is converted into the intensity | strength of electricity, such as a voltage, it will not specifically limit. Information on the time waveform of the intensity of the interference light is converted into information on the time waveform of the received light voltage by this light detection unit. Information on the time waveform of the received light voltage is sent to an information acquisition unit described below.

(Information acquisition unit)
An example of the configuration of the information acquisition unit 104 in the present embodiment will be described with reference to FIG. In an example of the information acquisition unit 104 in the present embodiment, time waveform information of analog received light voltage (information of interference light intensity time waveform) sent from the light detection unit 103 is digitally converted by the A / D converter 401. The received light voltage is converted into time waveform information. Information on the time waveform of the digital light reception voltage is stored in the memory 402 and sent to the calculation unit 403. The arithmetic unit 403 obtains the peak value from the time waveform of the digital light reception voltage, and obtains information on the object 113 by Fourier transforming the peak value. The information acquisition unit 104 has a Fourier transformer.

Next, an example of a flow for acquiring information on the object 113 in the information acquisition unit 104 will be described in detail with reference to FIGS. First, the light detection unit 103 receives light and acquires information on the time waveform of the voltage (S501 in FIG. 5 and FIG. 6A). Since it passes through the wavelength selector 105 described above, the time waveform of the intensity of the received light voltage also has an equal wave number interval. Next, the A / D board 401 converts the received light voltage from an analog signal to a digital signal (S502 in FIG. 5, FIG. 6B). The received light voltage information (interference light intensity information) converted into a digital signal is stored in the memory 402 (S503 in FIG. 5). This corresponds to storing data represented by white circles in FIG. The peak value of the received light voltage stored in the memory 402 is sampled, and the peak value is Fourier transformed by the calculation unit 403. Through such steps, object information can be obtained.

The sampling method of the peak value of the received light voltage stored in the memory 402 is not particularly limited, but it is necessary to acquire a significant maximum value that is not noise. For example, it is possible to provide a threshold value for a value larger than noise and extract a local maximum value having a value equal to or greater than the threshold value. As an example, when the information on the intensity of the received light voltage (interference light) stored in the memory is represented as shown in FIG. 7, when the received light voltage is a value higher than the received light voltage “5”, Is a peak value.

Threshold setting is not limited to a specific method. For example, when there are m maximum values of the transmittance of the wavelength selector 105 in the wavelength sweep band for acquiring a signal, m values are selected from the largest in the time waveform of the intensity of the received light voltage obtained. . The maximum value among the remaining maximum values not selected is regarded as the maximum value of noise, and a value larger than the maximum value of noise and the minimum value or more of the maximum values can be set as a threshold value. .

Further, when using the light source unit 101 whose wavelength sweep speed is known to be substantially constant, the wavelength of the maximum value of each transmittance of the wavelength selector is determined from the interval of the maximum value of the transmittance of the wavelength selector 105. The time when the light source unit 101 emits light can be estimated. Moreover, it can be set as the peak value for obtaining the maximum value among the local maximum values included in the time waveform obtained in the vicinity of each estimated time. Then, m can be selected from those having larger peak values.

Here, if the wavelength sweep speed of the light source unit 101 does not vary greatly, there should be no significant variation in the data time interval. Accordingly, as shown in FIG. 8, between the data of two points there is a time interval of the data (FIG. 8 time between t ₂ and time t ₄ of (a)) by a time interval of the signal obtained at the time of the surrounding If it is about twice open, it can be considered that the received light voltage obtained at that time (time t _{3 in} FIG. 8A) is “0”. Therefore, with respect to the sampling data to produce a sampled data inserting a 0 at time t _3. Such insertion of a “0” value is necessary particularly when an interference signal is acquired by performing differential detection.

That is, the information acquisition unit according to the present embodiment performs the time T ₁ when the intensity peak value (the peak value of the interference light intensity) P ₁ of the received light voltage is acquired, and the time after the time when the peak value P ₁ is acquired. in the time interval between time T _2, the peak value P ₂ is acquired, in which case the peak value in the vicinity of at least 1.99 times the average time interval ΔT that is obtained, preferably 1.9 times or more In some cases, calculation may be performed assuming that the intensity of the received light voltage (interference light intensity) at time T ′ between T ₁ and T ₂ is 0 (FIG. 8B). This wavelength sweep rate at time T _1, T ₂ If the varying within 10% of the wavelength sweep rate at time T ₀ or T _3, when it is more than 1.9 times the time interval ΔT of the average This is because the intensity of the received light voltage at time T ′ may be regarded as 0. Similarly, when it fluctuates within 1%, it is sufficient to consider that the intensity of the received light voltage is 0 when it is 1.99 times or more.

For example, when the average time interval is about twice (1.9 times or more and 2.1 times or less), the intensity of the received light voltage (interference light intensity) at time T ′ between T ₁ and T _2. Is assumed to be 0 (FIG. 8B).

Here, the peak value in the vicinity is, for example, the peak value (P ₀ ) at the time (T ₀ ) immediately before the peak value P 1 is acquired, and the peak value (T ₋₁ ) at the previous time (T ₋₁ ) ( P _-1), the peak value in one after the time _{_{(T 3) (P 3)}} , the peak value of the two after the time _{_{(T 4) (P 4)}} , a. At this time, the average time interval ΔT in which the neighboring peak values are acquired can be the average of the value of T ₀ -T _{-1 and} the value of T ₄ -T ₃ . Although the average time interval is calculated using the four peak values, the number of peak values used for the calculation may be more than that.

When the average time interval is about three times (2.9 times or more and 3.1 times or less), the intensity of the interference light at each time when the time interval between T ₁ and T ₂ is equally divided into three is 0. It is considered. Similarly, when it is about N times the average time interval, the intensity of the interference light at each time when the time interval between T ₁ and T ₂ is equally divided into N is considered to be zero.

When there is a point with the interference signal amplitude of 0 as described above, when the light detection unit 103 is a differential detection type, the light detection unit 103 outputs a voltage of 0 as described above. In the case of a simple light intensity detection type, the light amount of the non-interference component is detected and a non-zero value is output. Therefore, the interpolation of 0 value is an operation necessary when the light detection unit 103 is a differential detection type. Therefore, it is possible to detect the point of the interference component 0 as described above, for example, by measuring by using a differential detection type light detection unit and a simple light intensity detector together.

Also, for the data acquired at a time interval that is clearly shorter than the time interval of other data, for example, about half the time interval of the signal obtained at the surrounding time, the wavelength selector 105 There is a high possibility of sampling other than the maximum value of the transmittance (FIG. 8C). In this case, deleting the data which the time interval is jammed (data obtained at time t ₄ in FIG. 8 (c)). Through these, m pieces of sampling data having substantially equal time intervals can be formed. If there are a plurality of data with a short time interval, the data with a short time interval may be deleted a plurality of times as described above until the data with a short time interval disappears.

That is, the information acquisition unit according to the present embodiment includes the time T ₁ when the peak value of the intensity of the received light voltage (peak value of the intensity of the interference light) P ₁ and the time when the peak value P ₁ is acquired. When the time interval from the time T ₂ when the next peak value P ₂ is acquired is equal to or less than 0.9 times the average time interval ΔT at which the neighboring peak values are acquired, the peak value P ₂ Data need not be acquired (FIG. 8D). Here, the peak value in the vicinity is, for example, the peak value (P ₀ ) at the time (T ₀ ) immediately before the peak value P 1 is acquired, and the peak value (T ₋₁ ) at the previous time (T ₋₁ ) ( P _-1), the peak value in one after the time _{_{(T 3) (P 3)}} , the peak value of the two after the time _{_{(T 4) (P 4)}} , a. At this time, the average time interval ΔT in which the neighboring peak values are acquired can be the average of the value of T ₀ -T _{-1 and} the value of T ₄ -T ₃ . Although the average time interval is calculated using the four peak values, the number of peak values used for the calculation may be more than that.

(Light source)
In the present embodiment, the light source unit 101 is not particularly limited as long as it is a light source that changes the wavelength of light. In order to obtain information on the object 113 using the OCT apparatus, it is necessary to continuously change the wavelength of light emitted from the light source unit.

As the light source unit 101 in the present embodiment, for example, an external resonator type wavelength swept light source using a diffraction grating, a prism, or the like, or various external resonator type light sources using a Fabry-Perot tunable filter with a variable resonator length may be used. it can. Alternatively, an SSG-DBR that changes the wavelength using a sampled grating, a tunable MEMS-VCSEL, or the like can also be used. A fiber laser can also be used. The fiber laser may be a dispersion tuning method or a Fourier domain mode lock method.

As an external resonator type wavelength sweep light source using a diffraction grating, a prism, etc., a resonator is provided with a diffraction grating to disperse light, and a polygon mirror or a striped reflection mirror is provided on a rotating disk. A wavelength swept light source or the like may be used by continuously changing the wavelength of light emitted by using.

(object)
In the present embodiment, the object is a measurement target by the OCT apparatus according to the present embodiment, and the type is not particularly limited. For example, living bodies such as eyeballs, skin, and teeth can be mentioned.

(Use)
The OCT apparatus according to the present embodiment can be used for ophthalmic photography, dental photography, skin photography, etc. for obtaining a tomographic image of the fundus.

(Embodiment 2)
Another example of the OCT apparatus will be described. Descriptions of components of the OCT apparatus according to the present embodiment that are the same as those of the first embodiment are omitted here.

FIG. 1 shows a simple configuration of the OCT apparatus, but an optical system for differentially detecting interference signals as shown in FIG. 9 may be used. In FIG. 9, a wavelength tunable light source 901, an isolator 902, a reference light optical path fiber 906, a polarization controller 918, a fiber coupler 905 for branching light oscillated from the light source into reference light and irradiation light, and a reflection mirror 907 are provided. Deploy. Further, an inspection light optical path fiber 914, a polarization controller 919, an irradiation condensing optical system 915, and an irradiation position scanning mirror 908 that constitute a measurement unit of the object 909 are connected. In addition, a fiber coupler 903, a fiber coupler 904, a light receiving fiber 916, a light receiving fiber 917, a differential detector 910, a signal processing device 911 constituting an information acquisition unit, and an image output monitor 913 are connected. To do. Furthermore, an optical tomographic imaging apparatus can be configured by connecting a light source control device 912 that constitutes a light source unit.

Reference numerals

921, 922, 923, 924, 925, and 926 are collimators.

Since the Fabry-Perot filter 220, which is a wavelength selector, is provided in front of the differential detector 910, the light detected by the operation detector 910 is at equal wave intervals. Although FIG. 9 shows a configuration in which one Fabry-Perot filter 220 is provided, one light on the optical path between the collimator 922 and the collimator 924 and light between the collimator 923 and the collimator 925 are shown. A total of two configurations may be provided on the road. In this case, the two Fabry-Perot filters need to have the same FSR (Free Spectral Range, free spectral range). In this way, by using the differential detector 910 in the light detection unit and simultaneously inputting the interference signals from the two ports of the interference optical system, the common-mode noise can be eliminated, and the object with low noise can be eliminated. A tomographic image can be obtained.

(Embodiment 3)
In the third embodiment, an optical coherence tomography method will be described. The optical coherence tomography method described below is an example, and the present invention is not limited to this.

(Optical coherence tomography method)
An optical coherence tomography method according to the present embodiment is an optical tomography method using the above-described optical coherence tomography apparatus, the step of temporally changing the wavelength of light emitted from the light source unit, and the interference optics Receiving at least the interference light generated in the system by the light detection unit, and acquiring the object information based on the peak value of the time waveform of the intensity of the received interference light. The step of acquiring the object information preferably includes a step of acquiring a peak value of the time waveform of the intensity of the interference light and performing a Fourier transform. Further, when acquiring object information, an operation using the maximum entropy principle may be performed instead of Fourier transform.

Further, a step of transmitting data obtained by Fourier transform to the image display unit may be included. By having such a process, a tomographic image of the object to be measured can be displayed.

Hereinafter, although the Example of this invention is described using FIG. 1, this invention is not limited to these.

The configuration of the OCT apparatus according to the present example is as described in the first embodiment. However, a wavelength swept light source is used as the light source unit 101, a photo detector (hereinafter referred to as PD) is used as the light detection unit 103, and a Fabry-Perot etalon is used as the wavelength selector 105.

The wavelength swept light source sweeps the wavelength from 800 nm to 880 nm at a cycle of 5 ns and repeats this operation. This corresponds to a sweep frequency of 200 kHz. In the OCT apparatus according to the present embodiment, the optical path length from the point where the light from the light source unit 101 is emitted to the mirror 115 is made equal to the optical path length from the point where the light from the light source unit 101 is emitted to the surface of the object 113, Observation is performed from the surface of the object to a portion of 4 mm in the optical axis direction of the irradiation light.

When there is a single reflecting object at a position of 4 mm from the surface of the object in the direction of the optical axis of the irradiation light, the obtained spectrum of interference intensity becomes a signal whose intensity increases at every frequency of 37.5 GHz (FIG. 10). If this is regarded as a sine wave having a frequency of 37.5 GHz, in order to analyze the frequency component of this signal, it is necessary to sample the intensity value of the interference light at a frequency interval of at least half this frequency interval. That is, it is necessary to sample at a frequency interval of 18.75 GHz or less.

Assuming that the maximum depth is 4 mm in the optical axis direction of the irradiation light from the surface of the object, the frequency of the signal whose frequency is to be analyzed is a signal of 37.5 GHz or less, and thus the frequency of 18.75 GHz or less. If signals are acquired at intervals, a signal in a frequency band necessary for obtaining a tomographic image can be obtained.

In this embodiment, this sampling interval is defined by a Fabry-Perot etalon inserted in the optical path. Specifically, the interval between the maximum values of the transmittance of the Fabry-Perot etalon is set to be equal wave number intervals and less than 18.7 GHz. This is equivalent to setting the optical path length of the Fabry-Perot etalon to 8 mm or more. In this embodiment, the optical path length of the Fabry-Perot filter etalon is 8 mm. The optical path length may be longer than 8 mm.

Next, FIG. 11 shows a time waveform of the intensity of the received light voltage obtained by the PD using the OCT apparatus according to the present embodiment. The signal obtained by the light detection unit 103 has a waveform in which the transmittance of the Fabry-Perot filter is superimposed on the interference signal waveform. It is necessary to read the peak value in FIG. 11 and acquire the data as signal values at equal frequency intervals.

For this purpose, first, the time waveform of the voltage intensity acquired by light detection is taken into the memory of the information acquisition unit 104 via the AD converter. Next, the peak value is read from this data, and sampling data to be subjected to Fourier transform is produced. Here, a threshold value is provided for a value equal to or higher than noise, and a local maximum value having a value equal to or higher than the threshold value is extracted.

In this example, the maximum value m of the transmittance of the Fabry-Perot etalon is 1818. This is because the frequency interval between wavelengths of 800 nm and 880 nm is 34.07 THz, while the frequency interval of the maximum transmittance of the Fabry-Perot etalon is 18.74 GHz and the ratio thereof is 1818. Therefore, a tomographic image of an object can be acquired by performing Fourier transform using the local maximum values from 18 to 1818 received by the PD as sampling data.

The present invention is not limited to the above embodiment, and various changes and modifications can be made without departing from the spirit and scope of the present invention. Therefore, in order to make the scope of the present invention public, the following claims are attached.

This application claims priority based on Japanese Patent Application No. 2012-018821 filed on Jan. 31, 2012 and Japanese Patent Application No. 2013-009526 filed on Jan. 22, 2013. All the descriptions are incorporated herein.

DESCRIPTION OF SYMBOLS 101 Light source part 102 Interference optical system 103 Photodetection part 104 Information acquisition part 105 Wavelength selector

Claims

A light source unit that changes the wavelength of light;
An interference optical system that divides the light from the light source unit into irradiation light for irradiating the object and reference light, and generates reflected light of the light irradiated to the object and interference light by the reference light;
A light detector that receives the interference light;
Based on the time waveform of the intensity of the interference light, an information acquisition unit that acquires information of the object;
In an optical coherence tomography apparatus having
A wavelength selector provided on an optical path between the light source unit and the light detection unit and having wavelength selection characteristics at equal wave number intervals;
The information acquisition unit acquires a peak value of a temporal waveform of the intensity of the interference light, and acquires information on the object based on the acquired peak value.
The optical coherence tomography apparatus according to claim 1, wherein the information acquisition unit includes a Fourier transformer that acquires a peak value of a time waveform of the intensity of the interference light and performs a Fourier transform.
The optical coherence tomographic imaging apparatus according to claim 1 or 2, wherein the wavelength selector is provided on an optical path between the optical interference system and the light detection unit.
The optical coherence tomography apparatus according to any one of claims 1 to 3, wherein the wavelength selector has a maximum value of transmittance at equal wave number intervals.
5. The optical coherence tomography apparatus according to claim 4, wherein a line width of a maximum value of the transmittance of the wavelength selector is narrower than a line width of light generated from the light source unit.
The optical coherence tomography apparatus according to claim 4 or 5, wherein the wavelength selector is a Fabry-Perot filter.
The peak value of the time waveform of the intensity of the interference light acquired by the information acquisition unit is the data of the time waveform of the intensity of the interference light received by the light detection unit, from the one having the greater intensity of the interference light, The optical coherence tomographic imaging apparatus according to claim 1, wherein the number of the maximum of the transmittance of the wavelength selector is as many as the number.
The information acquisition unit includes a time T 1 at which the peak value P 1 of the intensity of interference light is acquired, and a time T 2 at which the next peak value P 2 after the time at which the peak value P 1 is acquired is acquired. Is equal to or greater than 1.9 times the average time interval ΔT from which the peak value in the vicinity is acquired, the intensity of the interference light at the time between T 1 and T 2 is zero. The optical coherence tomographic imaging apparatus according to any one of claims 1 to 7, characterized in that an operation that is considered to be performed is performed.
The information acquisition unit includes a time T 1 at which the peak value P 1 of the intensity of interference light is acquired, and a time T 2 at which the next peak value P 2 after the time at which the peak value P 1 is acquired is acquired. It claims 1 to 8 in the time interval, when the peak value in the vicinity is less than 0.9 times the average time interval ΔT acquired, characterized in that it does not get the data of the peak value P 2 The optical coherence tomographic imaging apparatus according to any one of the above.
An optical tomography method using the optical coherence tomography apparatus according to any one of claims 1 to 9,
Changing the wavelength of the light emitted from the light source part over time;
Receiving the interference light generated in the interference optical system by the light detection unit;
And a step of acquiring information of the object based on a peak value of a time waveform of the intensity of the received interference light.
11. The optical coherence tomographic imaging method according to claim 10, wherein the step of acquiring information on the object includes a step of acquiring a peak value of a time waveform of the intensity of the interference light and performing a Fourier transform.